βsheet tapes ribbons in tissue engineering

ABSTRACT

There is described a material comprising tapes, ribbons, fibrils or fibers characterized in that each of the ribbons, fibrils or fibers have an antiparallel arrangement of peptides in a β-sheet tape-like substructure.

CROSS REFERENCE TO RELATED APPLICATIONS

This is a divisional application of U.S. application Ser. No. 14/062,768filed on Oct. 24, 2013, which is a divisional of Ser. No. 12/729,046filed Mar. 22, 2010, now U.S. Pat. No. 8,586,539, which is acontinuation-in-part application of U.S. application Ser. No. 10/521,628filed Sep. 8, 2005, now U.S. Pat. No. 7,700,721 (both hereinincorporated by reference), which is the U.S. National Stage ofInternational Application No. PCT/GB2003/003016, filed Jul. 15, 2003(published in English under PCT Article 21(2)), which in turn claims thebenefit of Great Britain patent application no. 0216286.5 filed Jul. 15,2002.

FIELD

This disclosure relates to novel supramolecular aggregates, polymers andnetworks made by beta-sheet self-assembly of rationally-designedpeptides, and their uses as for example as responsive industrial fluids(oil exploration), as personal care products, as tissue reconstructiondevices (e.g., dental reconstructive devices), or as controlled drugdelivery systems.

BACKGROUND

International Patent Application No WO 96/31528 (Boden et al.) describesnovel rationally designed peptides which self-assemble in one dimensionto form beta sheet tape-like polymers. The tapes above a criticalpeptide concentration (typically above 0.3% v/v peptide) becomephysically entangled and gel their solutions in organic solvents or inwater (FIG. 1). The peptide gels possess the specific property of beingprogrammable to switch from the gel state to a fluid or stiffer gelstate in response to external chemical or physical triggers.

It has recently been found that the tapes having chemically distinctopposing surfaces can give rise to an hierarchy of other self-assembled,supramolecular structures as a function of increasing peptideconcentration: ribbons (two stacked tapes), fibrils (many ribbonsstacked together) and fibres (entwined fibrils) [1-3] (FIG. 2). Allthese beta-sheet polymers appear twisted because of the peptidechirality. A theoretical model has been developed which rationalisesthis self-assembly process of beta-sheet forming peptides using a set ofenergetic parameters ε_(j) (FIG. 1). The magnitudes of ε_(j) define thepeptide concentration ranges over which each type of polymer will bestable.

SUMMARY

We have shown that by appropriate peptide design we can produce tapes,ribbons, fibrils or fibres controllable by changes of the pH, the ionicstrength of the solution or temperature. In particular, peptides can bedesigned which self-assemble to form one or other of these polymers at acertain concentration and in a specific pH range, but which aretransformed into another polymer structure or dissociate into themonomeric random coil state in a different pH range, according to thespecific amino acid sequence of the peptide.

We have recently discovered that this hierarchy of polymers can beformed not only by a single type of peptide (homopeptide polymers), butalso by mixing complementary peptides together (alternatingco-polymers). For example, we have shown that peptide P₁₁-8 (Tablex 1Aand 1C) adopts monomeric random coil conformation and forms fluidisotropic solutions at pH<7 in water. This behaviour stems from thethree ornithine groups on the peptide. At pH lower than their effectivepKa, the ornothine side-chains are ionised, and the intermolecularelectrostatic repulsions generated by these positively charged groupsprevent beta-sheet self-assembly.

Thus, provided herein is a material comprising ribbons, fibrils orfibres characterised in that each of the ribbons, fibrils or fibres havean antiparallel arrangement of peptides in a β-sheet tape-likesubstructure.

When the material substantially comprises fibrils, the fibrils may becomprised in a network of fibrils interconnected at fibre-likejunctions.

Also provided is a material wherein the material comprises a selfassembling peptide (SAP) wherein the SAP forms a tape in an aqueousmedium and is made up of 3 or more polar/neutral amino acids and aplurality of charged amino acids.

The polar/neutral amino acids, which may be the same or different, andcan be selected from the group including glutamine, serine, asparagine,orthinine, cysteine, lysine, histidine, glutamic acid and threonine.

We further provide a material wherein the amino acids are positivelycharged and form a gel at a pH of higher than or equal to a neutral pH.Alternatively, we provide a material wherein the amino acids arenegatively charged and form a gel at a pH of lower than or equal to aneutral pH.

An exemplary material in this aspect of the disclosure is SAP P₁₁-8 (SEQID NO: 2).

We further provide a material wherein the amino acid chain is extendedto include a bioactive peptide sequence, or wherein the amino acid chainis attached to a therapeutically active molecule.

The material may comprise a SAP which forms ribbons and/or fibrils in anaqueous solution and wherein the SAP has a primary structure in which atleast 50% of the amino acids comprise an alternating structure of polarand apolar amino acids.

The polar amino acids include from 1 to 3 charged amino acids per 11amino acids. Preferably, the SAP is selected from the group P₁₁-9 (SEQID NO: 3), P₁₁-12 (SEQ ID NO: 4), P₁₁-15 (SEQ ID NO: 7), P₁₁-16 (SEQ IDNO: 8), P₁₁-17 (SEQ ID NO: 9), P₁₁-18 (SEQ ID NO: 10), P₁₁-19 (SEQ IDNO: 11) and P₁₁-20 (SEQ ID NO: 12).

Exemplary peptides of the present disclosure are recited in Tables 1A,1B, 1C and 1D.

TABLE 1A Primary structures of rationally designed peptides. PeptideName Primary Structure* SEQ ID NO: P₁₁-4 CH₃CO-Q-Q-R-F-E-W-E-F-E-Q-Q-NH₂ 1 P₁₁-8 CH₃CO-Q-Q-R-F-O-W-O-F-E-Q-Q-NH₂  2 P₁₁-9CH₃CO-S-S-R-F-E-W-E-F-E-S-S-NH₂  3 P₁₁-12CH₃CO-S-S-R-F-O-W-O-F-E-S-S-NH₂  4 P₁₁-13CH₃CO-E-Q-E-F-E-W-E-F-E-Q-E-HN₂  5 P₁₁-14CH₃CO-Q-Q-O-F-O-W-O-F-O-Q-Q-NH₂  6 P₁₁-15CH₃CO-N-N-R-F-E-W-E-F-E-N-N-NH₂  7 P₁₁-16CH₃CO-N-N-R-F-O-W-O-F-E-N-N-NH₂  8 P₁₁-17CH₃CO-T-T-R-F-E-W-E-F-E-T-T-NH₂  9 P₁₁-18CH₃CO-T-T-R-F-O-W-O-F-E-T-T-NH₂ 10 P₁₁-19CH₃CO-Q-Q-R-Q-O-Q-O-Q-E-Q-Q-NH₂ 11 P₁₁-20CH₃CO-Q-Q-R-Q-E-Q-E-Q-E-Q-Q-NH₂ 12 *The N- and C- termini of thepeptides are always blocked with CH₃CO- and NH₂- respectively. Osymbolizes ornithine amino acid side chains.

TABLE 1B Amphiphilic self assembling peptides carrying a net negative 2charge in physiological solution. Net Pep- Charge Polar tide at pH AminoName 7.5 Acid Peptide Structure (SEQ ID NO:) P₁₁-9 −2 Serine

(3) P₁₁-15 −2 Aspar- agine

(7) P₁₁-17 −2 Threo- nine

(9)

TABLE 1C Amphiphilic self assembling peptides carrying a net positive 2charge in physiological solution. Net Pep- Charge Polar tide at pH AminoName 7.5 Acid Peptide Structure (SEQ ID NO:) P₁₁-8 +2 Gluta- mine

(2) P₁₁-12 +2 Serine

(4) P₁₁-16 +2 Aspar- agine

(8) P₁₁-18 +2 Threo- nine

(10)

TABLE 1D Polar self assembling peptides carrying a net negative 2 chargein physiological solution. Net Pep- Charge Polar tide at pH Amino Name7.5 Acid Peptide Structure (SEQ ID NO:) P₁₁-19 +2 Gluta- mine

(11) P₁₁-20 −2 Gluta- mine

(12)

The peptides provided herein are preferably 11 residues in length andhave a conserved arginine residue at position 3.

Preferably, the amino acid residues at positions 1 and 2 are the sameand are selected from the group comprising serine (SS), glutamine (QQ),threonine (TT) and asparagines (NN),

Preferably, the amino acid residues at positions 10 and 11 are the sameand are selected from the group comprising serine (SS), glutamine (QQ),threonine (TT) and asparagines (NN),

Preferably, the amino acid residues at positions 1 and 2 and 10 and 11are the same so that they are all either serine (SS), glutamine (QQ),threonine (TT) or asparagines (NN).

Preferably, the amino acid residue at position 4 is either phenylalanineor glutamine.

Preferably, the amino acid residues at positions 4 and 5 are selectedfrom the pairs of the group comprising phenylalanine and glutamic acid,phenylalanine and ornithine, glutamine and glutamic acid and glutamineand ornithine.

The material may be suitable for use in, inter alia, tissue engineering,cell culture medium, and/or dental treatment.

We also provide a material wherein the material comprises a selfassembling peptide (SAP) wherein the SAP forms a tape in an aqueousmedium and is made up of 3 or more polar/neutral amino acids and aplurality of charged amino acids.

In some examples, the SAP is isolated. An “isolated” biologicalcomponent (such as a protein) has been substantially separated orpurified away from other biological components present in the cell of anorganism, or the organism itself, in which the component may naturallyoccur, such as other chromosomal and extra-chromosomal DNA and RNA,proteins and cells. In addition, proteins that have been “isolated”include proteins purified by standard purification methods. The termalso embraces proteins prepared by recombinant expression in a host cellas well as chemically synthesized proteins. For example, an isolated SAPis one that is substantially separated from other peptides.

The polar/neutral amino acids, which may be the same or different, maybe selected from the group including glutamine, serine, asparagine,orthinine, cysteine, lysine, histidine, glutamic acid and threonine.

In one example, the peptides have a polar amino acid selected from thegroup consisting of serine, asparagines, threonine and glutamine.

The apolar amino acids, which may be the same or different, are selectedfrom the group including phenylalanine, tryptophan, valine, leucine,isoleucine and methionine.

We further provide a material wherein the amino acid chain is extendedto include a bioactive peptide sequence, or wherein the amino acid chainis attached to a therapeutically active molecule.

In one example, in this aspect of the disclosure the SAP is P₁₁-8 (SEQID NO: 2).

We also provide a material wherein the SAP is soluble in a highly ionicmedium. In this aspect of the disclosure, the SAP may comprise a ratioof net charged amino acids to total amino acids of from 1:11 to 4:11.

The material may be suitable for use in, inter alia, tissue engineering,cell culture medium, and/or dental treatment.

We further provide a material wherein the complementary peptide tapesare made up of 3 or more polar amino acids of which some are chargedamino acids wherein the ratio of charged amino acids to total aminoacids is 3:11 or greater.

We further provide a material wherein the amino acid chain is extendedto include a bioactive peptide sequence, or wherein the amino acid chainis attached to a therapeutically active molecule.

The material may be suitable for use in, inter alia, tissue engineering,cell culture medium, and/or dental treatment.

Thus, according to a further feature of the disclosure we providealternate co-polymer beta-sheet polymeric tapes, ribbons, fibrils andfibres made by the self-assembly of more than one complementarypeptides. The complementarity of the peptide may be originating fromtheir charges e.g., net positive charge on one peptide and net negativecharge on the other peptide.

Also provided is a composition that includes ribbons, fibrils or fibresand a physiological concentration of salt (such as 120 to 160 mM NaCl,for example 140 to 150 mM NaCl or 145 to 150 mM NaCl, for example about145 mM NaCl), wherein the composition is at a physiological pH (such aspH 7 to 8, for example pH 7.2 to 7.6, or pH 7.4 or pH 7.5), and whereinthe peptide is present at a concentration of at least 15 mg/ml in thecomposition (for example 15 mg/ml to 100 mg/ml, 15 mg/ml to 60 mg/ml, 15mg/ml to 50 mg/ml, 15 mg/ml to 35 mg/ml, 20 mg/ml to 50 mg/ml or 20mg/ml to 35 mg/ml). Each of the ribbons, fibrils or fibres has anantiparallel arrangement of peptides in a β-sheet tape-like substructureat physiological pH and physiological salt concentrations, wherein eachpeptide or pair of complementary peptides comprises a net −2 or a +2charge, and wherein the peptide is selected from the group comprisingP₁₁-8, P₁₁-9, P₁₁-12, P₁₁-15, P₁₁-16, P₁₁-17, P₁₁-18 and P₁₁-20 as setforth in Table 1A.

The foregoing and other features of the disclosure will become moreapparent from the following description of the figures.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1: Schematic representation of peptides in beta-strand conformation(represented as vertical lines) hydrogen bonding in one dimension witheach other to form long self-assembling beta-sheet tapes. The width ofthe tape is determined by the length of the peptide molecules. Thethickness of the tape is equal to the thickness of a beta-strand. Thesurface properties of the tapes are defined by the end groups of thepeptide amino acid side-chains. The tapes are also shown to entangle toform a gel network in a good solvent.

FIG. 2. Model of hierarchical self-assembly of beta-sheet formingpeptides. Each peptide in beta-strand conformation, is depicted as achiral rod-like unit (a). Local arrangements (c-f) and the correspondingglobal equilibrium conformations (c′-f′) for the hierarchicalself-assembling structures formed in solutions of chiral molecules (a),which have complementary donor and acceptor groups, shown by arrows, viawhich they interact and align to form tapes (c). The black and the whitesurfaces of the rod (a) are reflected in the sides of the helical tape(c) which is chosen to curl towards the black side (c′). The outer sidesof the twisted ribbon (d), of the fibril (e) and of the fibre (f) areall white. One of the fibrils in the fibre (f′) is drawn with darkershade for clarity. (e) & (f) show the front views of the edges offibrils and fibres, respectively. Geometrical sizes (the numbers inparentheses show the values of the corresponding geometric sizes forP₁₁-I and P₁₁-II peptides, based on X-ray diffraction data and molecularmodelling): inter-rod separation in a beta-sheet tape b₂ (b₂=0.47 nm);tape width, equal to the length of a rod, b₁ (b₁=4 nm); inter-ribbondistance in the fibril, α (α=1.6-2 nm for P₁₁-I, and α=2-2.4 nm forP₁₁-II).

FIG. 3: Alternating copeptide polymeric gels.

FIG. 4: Schematic representation of orientation of the semi-rigidfibrils in solution to form nematic liquid crystalline solutions. Athigher peptide concentration, the fibrils entwine frequently with eachother to form fibre-like junctions and cause formation of an anisotropicthree-dimensional matrix and gelation of the liquid crystallinesolution.

FIGS. 5A-5D: Digital optical micrograph pictures of a positive control(A) of a collagen gel and murine L929 fibroblasts, a negative control(B) and gels with peptides P₁₁-15 (C) and P₁₁-16 (D) and the murinefibroblasts growing in contact with and onto the peptide gel matrix.

FIGS. 6A-6D: Digital TEM images of fibrils formed in a self supportinggel by peptides P₁₁-4 (A), P₁₁-9 (B), P₁₁-15 (C) and P₁₁-17 (D).

FIGS. 7A-7D Digital TEM images of fibrils formed in a self supportinggel by peptides P₁₁-8 (A), P₁₁-12 (B), P₁₁-16 (C) and P₁₁-18 (D).

FIGS. 8A and 8B Show digital TEM images of fibrils formed in a selfsupporting gel by peptide P₁₁-19 (A) and peptide P₁₁-20 (B).

FIG. 9 Shows de novo precipitation of HA inside peptide gels for some ofthe peptides of the disclosure.

FIG. 10 is a plot showing the effect of increasing negative or positivecharge on gel formation.

SEQUENCE LISTING

The nucleic and amino acid sequences listed in the accompanying sequencelisting are shown using standard letter abbreviations for nucleotidebases, and three letter code for amino acids, as defined in 37 C.F.R.1.822. Only one strand of each nucleic acid sequence is shown, but thecomplementary strand is understood as included by any reference to thedisplayed strand. The Sequence Listing is submitted as an ASCII textfile in the form of the file named “Sequence.txt” (˜8 kb), which wascreated on Oct. 20, 2015, which is incorporated by reference herein. Inthe accompanying sequence listing:

SEQ ID NO: 1 is the amino acid sequence for P11-4.

SEQ ID NO: 2 is the amino acid sequence for P11-8.

SEQ ID NO: 3 is the amino acid sequence for P11-9.

SEQ ID NO: 4 is the amino acid sequence for P11-12.

SEQ ID NO: 5 is the amino acid sequence for P11-13.

SEQ ID NO: 6 is the amino acid sequence for P11-14.

SEQ ID NO: 7 is the amino acid sequence for P11-15.

SEQ ID NO: 8 is the amino acid sequence for P11-16.

SEQ ID NO: 9 is the amino acid sequence for P11-17.

SEQ ID NO: 10 is the amino acid sequence for P11-18.

SEQ ID NO: 11 is the amino acid sequence for P11-19.

SEQ ID NO: 12 is the amino acid sequence for P11-20.

SEQ ID NO: 13 is the amino acid sequence for P11-2.

SEQ ID NO: 14 is the amino acid sequence for P11-21.

SEQ ID NO: 15 is the amino acid sequence for P11-22.

SEQ ID NO: 16 is the amino acid sequence for P11-23.

SEQ ID NO: 17 is the amino acid sequence for P11-3.

SEQ ID NO: 18 is the amino acid sequence for P11-5.

DETAILED DESCRIPTION

The singular forms “a,” “an,” and “the” refer to one or more than one,unless the context clearly dictates otherwise. For example, the term“comprising a peptide” includes single or plural peptide and isconsidered equivalent to the phrase “comprising at least one peptide.”The term “or” refers to a single element of stated alternative elementsor a combination of two or more elements, unless the context clearlyindicates otherwise. As used herein, “comprises” means “includes.” Thus,“comprising A or B,” means “including A, B, or A and B,” withoutexcluding additional elements.

Unless explained otherwise, all technical and scientific terms usedherein have the same meaning as commonly understood to one of ordinaryskill in the art to which this disclosure belongs. Although methods andmaterials similar or equivalent to those described herein can be used inthe practice or testing of the present disclosure, suitable methods andmaterials are described below. The materials, methods, and examples areillustrative only and not intended to be limiting.

The tapes, ribbons, fibrils and fibres are increasingly more rigidstructures [1]. For example we have found that the persistence length{tilde over (l)} of single tapes formed by an 11-residue peptide P₁₁-1in water is ca 0.3 μm, whilst the persistence lengths of ribbons andfibrils formed by a variant P₁₁-2 peptide in water are 1 and 20-70 μmrespectively (Table 1).

We have also shown that above a certain peptide concentration c_(I/N)(isotropic to nematic transition concentration) the semi-rigid ribbons,fibrils and fibres can align and thus transform their initiallyisotropic solution into a nematic liquid crystalline solution. Thetransition of the solution to the nematic liquid crystalline statehappens at lower concentrations for more rigid polymers. For example,the nematic transition for solutions of ribbons of P₁₁-1 peptide occursat c_(I/N)≈13 mM, whilst the nematic transition for solutions of themuch more rigid fibrils of P₁₁-2 peptide occurs at c_(I/N)≈0.9 mM.

We have also shown that as the peptide concentration increases evenfurther there is a second transition from a fluid nematic liquidcrystalline solution to a self-supporting nematic gel, which is formedby the entwining of the fibrils (FIG. 4).

We have discovered that the alignment of these polymers (tapes, ribbons,fibrils and fibres) can be improved significantly by shearing orapplication of external magnetic field to the peptide solution.Subsequent gelation locks the aligned polymers into place and preservestheir alignment for a long time (typically weeks) even after the polymersolution is removed from the magnetic field or after the end ofshearing. Shearing or external magnetic field (superconducting magnetwith a field strength of 7 T) have been found indeed to improve thealignment of fibrils in aqueous solutions of P₁₁-2 peptide, as shown bymonitoring the birefringence of the solution using cross polars. Theimproved polymer alignment in solution has been preserved for severalweeks after the end of shearing or of the application of the magneticfield.

Provided is a method of producing nematic liquid crystalline solutionsand gels of homopeptide or alternating copeptide beta-sheet tapes,ribbons, fibrils or fibres with improved polymer alignment and thusimproved optical properties (i.e., increased liquid crystallinity andbirefringence), by shearing the peptide solutions or by subjecting themto other external forces such as electric and magnetic fields.

These peptide liquid crystalline solutions and gels can be formed inorganic solvents or in water depending on the peptide design. The designof the peptide primary structure is necessary to achieve compatibilitybetween the surface properties of the peptide polymers and the solvent.For example, self-assembling beta-sheet forming peptides withpredominantly hydrophobic amino acid side-chains are required to formnematic solutions and gels in moderately polar solvents, whilst peptideswhich form tapes with at least one polar side are required to obtainnematic solutions and gels in water.

The fibrils and fibres are alignable and can therefore form nematicgels. Therefore, the fibrils and fibres can be spun to make, forexample, high tensile strength fibres, cf. Kevlar®. Also, they can beused to make highly ordered scaffolds for tissue engineering ortemplates for the growth of inorganic matrices, or as matrices for thealignment of biomolecules, e.g., in NMR spectroscopy.

Until recently, formation of these polymers has been limited torelatively simple solutions (e.g., pure solvents or low ionic strengthsolutions). We have now discovered that it is possible to rationallydesign peptides which will form soluble polymers (e.g., tape, ribbons,fibrils and fibres) in more complex biologically relevant fluids, forexample in cell media. These are complex mixtures used for growing andmaintaining cells, because they mimic the natural environment of thecell in vivo (for the composition of typical cell media see FIG. 5). Theissue of polymer solubility in these media is of practical importance.The reason is that biological fluids and cell media are characterised byrelatively high ionic strength, equal to about 145 mM NaCl, which tendsto cause polymers to precipitate. We have discovered that in order toproduce soluble peptide polymers in these solutions, it is necessary tobuild an appropriate degree of repulsion between the polymers to keepthem apart in solution. Stable three-dimensional gel scaffolds can beproduced in cell media in this way, which precipitate from solution.

The stages of peptide design for formation of soluble beta-sheetpolymers and gel scaffolds in cell media are:

-   -   1) for production of single tapes, design the peptide following        the criteria in the International Patent Application No.        PCT/GB96/00743. To produce stable single tapes in cell media,        both sides of tapes should be covered by predominantly polar        groups.    -   2) for production of ribbons, fibrils and fibres, one sides of        the tape should be different from the other, e.g. one        predominantly polar and the other predominantly apolar. The        polar sides should also be able to weakly interact with each        other e.g. through hydrogen-bonding sites provided for example        by glutamine or asparagines side chains.    -   3) To ensure all these polymers are soluble in cell media, some        repulsion between polymers must be created. This can be        electrostatic repulsion between like charges on the polymers.        Alternatively, it can be steric repulsions created by flexible        solvophilic chains decorating the peptide polymers such as        polyethylene glycol chains when water is the preferred solvent.        These PEG segments can be attached on amino acid side-chains or        on the peptide termini.

By way of illustration, we include the following example:

A large number (dozens) of systematically varied peptides (typically7-30 residues long) have been studied for soluble polymer and gelformation in cell media. All of these peptides can self-assemble to formbeta-sheet polymers in certain low-ionic strength media, but most werefound to precipitate out of solution in cell media. Only peptides with aapproximate net +2 or −2 charge per peptide at physiological pH=7.5,were able to form soluble polymers and gel cell media (The amount of netcharge necessary per peptide to keep its polymers soluble in cell mediawill vary depending on the overall surface properties and solubility ofthe peptide tapes it forms). Amongst the peptides studied, peptides with+3 or −3 net charge per molecule exhibited only limited self-assemblingcapabilities in cell media at peptide concentration higher than 10 mg/mland did not produce a gel matrix at any peptide concentration. Peptideswith a +4 or −4 net charge per molecule did not self-assemble in cellmedia. These peptides retained a predominantly monomeric state and theirsolutions in cell media were fluids up to around 40 mg/ml peptideconcentration.

For example, the rationally designed peptide P₁₁-8 in low ionic strengthmedia at pH=7.5 does not self-assemble (peptide concentrations up to 10mg/ml). However, when 145 mM NaCl is added in the solution or when thepeptide is dissolved in cell media, it forms twisted beta-sheet fibrils,with narrow width of 4-5 nm, wide width of 12-15 nm, full pitch of200-300 nm, and length of several micrometers.

The fibrils entwine and form a three dimensional network and turn theirsolution in cell media into a homogeneous self-supporting gel at peptideconcentration higher than 15 mg/ml. The gel remains stable for at leastseveral weeks at room temperature.

The gel can be broken by mechanical agitation. The time it takes toreform depends on the peptide concentration, ranging from seconds for a35 mg/ml peptide gel, to hours for a 15 mg/ml peptide gel.

Similar behaviour was found for the rationally designed peptide P₁₁-8(Table 1) in cell media. The main difference between fibrils of P₁₁-15and of P₁₁-8 is that those formed by P₁₁-15 have a net −2 negativecharge per peptide at pH=7.5, whilst those formed by P₁₁-8 have net +2charge per peptide at pH=7.5.

Thus, peptide fibrils and gels with a variety of chemical properties canbe produced by peptide design. For example, the type of charge (+ or −)of the polymer may be crucial for the polymer matrix-cell interactions.The nature of the neutral polar side-chains can also be varied tofine-tune and maximise the favourable polymer-cell interactions, and thepolymer stability in vivo.

The fibrils and gels of P₁₁-3 and P₁₁-8 in cell media were found toreform after sterilisation using an autoclave. Thus autoclaving is aviable method to sterilise these peptide gels. This is significant,since sterilisation is a prerequisite for the use of these materialswith cells in vitro or in vivo. Other alternative sterilisation methodsthat can also be used are filtration of the initially monomeric peptidesolutions or gamma irradiation.

Although the peptide design procedure stated above can be used to designeither tapes or higher order aggregates (i.e., ribbons, fibrils andfibres) in cell media, the more robust fibrils and fibres arepotentially more useful for production of peptide scaffolds for tissueengineering. The reason is that the fibrils being much strongerstructural units than e.g., tapes, can support cells in three dimensionswithout significant breakage for a long time. In addition, the highlypacked nature of the fibrils, protects the peptides from enzymaticdegradation, and can increase significantly the lifetime of the scaffoldin vivo.

The peptide gels are formed with a very low peptide concentration(typically at or above 15 mg/ml), which corresponds to 0.01 volumefraction of peptide and 0.99 volume fraction of solvent in the gel,which means that the gels contain mainly solvent. Thus, encapsulatedcells in these gels, have a lot of room available to grow, tocommunicate with each other and nutrients, oxygen, and variousmetabolites can diffuse almost freely in and out of the gel network.

Injection of P₁₁-3 and P₁₁-8 peptide solutions in cell media in mice hasshown no effect of the presence of the peptide in the tissue surroundingthe injection site as judged by histology after two and eight weeksfollowing the peptide injection.

The opportunities that these new biomaterials provide for tissueengineering in vitro and in vivo are enormous. A large number ofdifferent cells can be encapsulated in these polymer scaffolds.

Peptides can be designed to have a self-assembling domain followed by atleast one bioactive domain. Thus, polymeric gel scaffolds can be formedin cell media, decorated with specific bioactive sequences (e.g., RGDsequence) which will control the interactions of the scaffold with aparticular type of cell, and also influence the growth differentiationstate and function of the encapsulated cells.

The peptide polymers (especially so the more rigid fibrils and fibres)can be preferentially aligned by shearing or application of magneticfield. Thus, anisotropic polymer scaffolds can be obtained which whenthey are seeded with cells, they can be particularly important for thecontrol of cell type, cell-cell interactions and shape of the growingtissue.

The cells can be encapsulated in the polymer matrix in a variety ofdifferent ways. For example:

-   -   1) disruption of gel by mechanical agitation, mixing with the        cells, and encapsulation of the cells as the gel matrix reforms        around them.    -   2) Mix the cells with an initially fluid monomeric peptide        solution in cell media, followed by triggered gel formation. The        trigger can be changes of the ionic strength, small pH changes,        or addition of counter ions such as Ca+2.    -   3) Possibly the most effective way of encapsulating cells in the        peptide scaffolds is using alternating copeptides. We have        observed the following:

Peptides P₁₁-6 and P₁₁-7 on their own in cell medium do notself-assemble to form long beta-sheet polymers, and for this reasontheir solution in cell media is fluid-like rather than gel-like. Theirlack of self-assembly is attributed to their high net positive andnegative charges per peptide P: −6 for P₁₁-6 and +4 for P₁₁-7. Whensolutions of these two peptides in cell media (peptide concentrationgreater than 10 mg/ml) are mixed together they spontaneously transforminto a self-supporting gel, owing to the formation of heteropeptidebeta-sheet polymers by these complementary interacting peptides.

Thus, it is seen that the alternating copeptide systems offer a uniqueway of encapsulating cells in the peptide scaffolds without the need tochange the pH, ionic strength and counter ion concentration of the cellsolutions. This can be done by mixing the cells with one of the initialmonomeric peptide solutions, and subsequently adding the complementarypeptide solution.

The heteropeptide polymers scaffolds also offer the advantage ofcombining different functionalities on the same polymers, and extendingthe chemical and periodic features of homopeptide polymers. For exampleone peptide component of the polymer may have a bioactive peptide boundto it, whilst its other peptide compound may have a drug molecule boundon it.

The ribbons, fibrils and/or fibres of the disclosure exhibit significanttensile strength, controlled, inter alia, by how many tapes make up theribbons, fibrils or fibres, especially in the longitudinal direction ofthe fibril or fibre. Such strength has been estimated to be in the orderof that of a conventional covalent bond. Furthermore, since the fibrilsand/or fibres are biodegradable, because of their peptide content, theyare especially advantageous in that they may be constructed into abiodegradable scaffold. Such scaffolds may comprise a weave, knit orplait of the fibrils or fibres of the disclosure.

Scaffolds can also be constructed using a combination of the peptidepolymers and other commercial polymers (such as cotton and wool fibres),to obtain materials with a desirable combination of mechanical, chemicaland biochemical properties, and low production cost.

Alignment of the microscopic fibrils followed by subsequent lateralassociation of the fibrils can result in the formation of macroscopicoriented fibre mats.

The peptide fibrils and/or fibres can be engineered to control thechemical and bioactive properties of synthetic polymer fibres. Themethodology has the advantage of harnessing and combining existingexpertise on manufacturing at low-cost well controlled fibrousstructures with desirable mechanical properties, with the opportunity ofdesigning their bioactivity, biocompatibility and other chemicalproperties. Such new materials can have exciting applications inbiomedical fields such as in tissue engineering, wound healing andtissue adhesion.

Products and Applications

INDUSTRIAL APPLICATIONS

Modification of the physical and chemical properties of a surface in acontrolled way, e.g., wetting properties; for example, for anti-icingapplications.

Also for controlling the interaction of oil/water with clay surfaces,and the stabilising the clay itself, an important issue when, e.g.,dealing with fractures in oil wells. The stability of the peptidepolymers can be controlled by peptide design. Thus, by increasing thenumber of amino acid residues per peptide and also the number offavourable intermolecular interactions between amino acid side-chains,peptide polymers with increased stability and strength can be obtained.In addition, ribbons, fibrils and fibres can be increasingly more stablepolymers compared to single tapes. Thus, the right polymers can beproduced by peptide design to form gels stable in the high temperatureof the oil wells. These gels can for example provide significantmechanical support at a specific site of the oil well.

Receptor or receptor binding sites can be engineered by peptide designinto the ribbons, fibrils and/or fibres, providing materials for use assensors or as biocatalysts, or as separation media in biotechnologyapplications.

The peptide tapes, ribbons, fibrils and fibres can be used as templatesfor the production of nanostructured inorganic materials with chiralpores. The dimensions, pitch and chirality of the pores can becontrolled by peptide design to control the properties of the polymeraggregate. The orientation of the pores can also be controlled byalignment of the polymers in nematic states. These nanostructuredmaterials have important applications as chiral separation media.

The fibres of the disclosure are advantageous because, inter alia, theypossess similar properties to other known peptide fibres, for example,KEVLAR® which consists of long molecular chains produced frompoly-paraphenylene terephthalamide. Thus the fibres of the disclosureexhibit the following features; high tensile strength at low weight,high modulus, high chemical resistance, high toughness, high cutresistance, low elongation to break, low thermal shrinkage, highdimensional stability, flame resistant and self extinguishing.

Therefore, the fibres of the disclosure can be processed into variousforms, for example, continuous filament yarns, staple, floc, cord andfabric.

The processed fibres may possess the following characteristics:continuous filament yarn, high tensile strength, processable onconventional looms, twisters, cord forming, stranding and servingequipment; staple, very high cut resistance, spun on conventional cottonor worsted spinning equipment, precision cut short fibres, processableon felting and spun lace equipment; pulp-wet and dry, floc, precisioncut short fibres, high surface area, miscible in blend composites,thermal resistance, excellent friction and wear resistance; cord, hightensile strength and modulus at low specific weight, retention ofphysical properties at high and low temperature extremes, very low heatshrinkage, very low creep, good fatigue resistance; fabric, excellentballistic performance at low weights; and excellent resistance to cutsand protrusion combined with comfortable wear and excellent friction andwear performance against other materials.

The peptide fibrils and fibres of the disclosure may have a variety ofapplications, for example, in adhesives and sealants, e.g. thixotropes;in ballistics and defence, e.g., anti-mine boots, gloves—cut resistancepolice and military, composite helmets, and vests—bullet andfragmentation; in belts and hoses, e.g. automotive heating/coolingsystems, automotive and industrial hoses, and automotive and industrialsynchronous and power transmission belts; in composites, e.g., aircraftstructural body parts and cabin panels, boats, and sporting goods; infibre optic and electro-mechanical cables, e.g., communication and datatransmission cables, ignition wires, and submarine, aerostat and robotictethers; in friction products and gaskets, e.g., asbestos replacement,automotive and industrial gaskets for high pressure and high temperatureenvironments, brake pads, and clutch linings; in protective apparel,e.g. boots, chain saw chaps, cut resistant industrial gloves,helmets—fireman and consumer (bicycle), and thermal and cut protectiveaprons, sleeves, etc; in tires, e.g. aircraft, automobiles, off-road,race, and trucks; and in ropes and cables, e.g., antennae guy wires,fish line, industrial and marine utility ropes, lifting slings, mooringand emergency tow lines, netting and webbing, and pull tapes.

Biomedical and Biomaterial Applications

Biocompatible Surfaces:

Bioresponsive and biocompatible surfaces to promote or to preventadhesion, spreading and growth of endothelial cells in medical implantmaterials. Biocompatible surface coatings for devices such as stents,valves and other structures introduced into biological systems.

Tissue Engineering:

The peptide fibrils and/or fibres of the disclosure can be used in theconstruction of a biodegradable three-dimensional scaffold for use inattaching cells to produce various tissues in vivo and in vitro.

Thus according to a further feature of the disclosure we provide athree-dimensional scaffold comprising fibres or fibrils of thedisclosure in cell medium. As mentioned above such scaffolds of thepeptide fibrils and/or fibres are advantageous in that they can be usedto support cells in the growth and/or repair of tissue. The nature ofsuch cells may vary depending upon the nature of the tissue of interest.For example, the cells may be ligamentum cells for growing newligaments, tenocytes for growing new tendon. Alternatively, the cellsmay be chondrocytes and/or other stromal cells, such as chondrocyteprogenitor cells.

Therefore, according to a yet further feature of the disclosure weprovide a three-dimensional scaffold comprising fibres or fibrils ashereinbefore described which scaffold is seeded with cells.

The methods of the disclosure therefore result in the efficientproduction of new ligament, tendon, cartilage, bone, skin, etc in vivo.

The cells may themselves be cultured in the matrix in vitro or in vivo.The cells may be introduced into the implant scaffold before, during orafter implantation of the scaffold. The newly grown tissue can be usedto hold the scaffold in place at the site of implantation and also mayprovide a source of cells for attachment to the scaffold in vivo.

The ability of the polymers to break allowing the free ends to selfassemble enables, for example, scaffolds to be formed in situ and alsoto respond (by breaking and reforming) to the growing tissue. Alsomonomeric peptides may be injected at the site of choice and thenchemically triggered to create, for example, a gel in situ.

Thus, according to a further feature of the disclosure we provide amethod of tissue repair which comprises seeding a three-dimensionalfibre matrix as hereinbefore described with appropriate cells.

For a tendon or ligament to be constructed, successfully implanted, andfunction, the matrices must have sufficient surface area and exposure tonutrients such that cellular growth and differentiation can occurfollowing implantation. The organisation of the tissue may be regulatedby the microstructure of the matrix. Specific pore sizes and structuresmay be utilised to control the pattern and extent of fibrovasculartissue in growth from the host, as well as the organisation of theimplanted cells. The surface geometry and chemistry of the scaffoldmatrix may be regulated to control the adhesion, organisation, andfunction of implanted cells or host cells.

In an exemplary embodiment, the scaffold matrix is formed of peptideshaving a fibrous structure which has sufficient interstitial spacing toallow for free diffusion of nutrients and gases to cells attached to thematrix surface until vascularisation and engraftment of new tissueoccurs. The interstitial spacing is typically in the range of 50 nm to300 microns. As used herein, “fibrous” includes one or more fibres thatis entwined with itself, multiple fibres in a woven or non-woven mesh,and sponge-like devices.

Nerve Tissue Engineering:

The fibrils and/or fibres can be used to provide paths/tracks, tocontrol and guide the direction of growth or movement of molecules orcells. This may be useful for nerve tissue repair as well as for growthand formation of bone tissue (tissue engineering).

Bone Tissue Engineering:

Biomineralisation using the peptide ribbons, fibrils and/or fibres as atemplate for the nucleation and growth of inorganic materials isimportant in bone tissue engineering and dental applications etc. Theself assembled peptide structures have been shown to be effective astemplates for hydroxyapatite crystallisation, as shown in the laterexamples.

Self-assembling peptides may increase mineral gain via their ability tonucleate hydroxyapatite de novo and/or by decreasing mineral dissolutionvia stabilisation of mineral surfaces. They are therefore candidatematerials for use in both caries treatment and prevention and intreatment or prevention of bone deterioration, such as that experiencedin osteoporosis.

The use of peptides, e.g., self assembling peptides (SAPs), as scaffoldsin in situ tissue engineering of bone is novel per se.

Thus according to a further aspect of the disclosure provided is amethod of tissue engineering, e.g., tissue repair, such as of bonerepair, which comprises the use of a SAP as a scaffold.

Artificial Skin:

Network structures formed from the peptide ribbons, fibrils or fibrescan be used to generate artificial skin or to promote skin re-growth invivo.

Drug Delivery:

pH and ion responsive ribbons, fibrils, fibres, gels or liquid crystalsare potentially useful in drug encapsulation and release and bydesigning an appropriate network programmable release rates may beachieved.

Personal Care Products

Dental Applications:

Peptide ribbons, fibrils and/or fibres are of use in the protection ofteeth, as carriers for delivery of active substances to promote dentalrepair, as templates/scaffolds for the in situ nucleation ofhydroxyapatite within tooth porosities (e.g., caries lesions, dentine),as agents for the treatment and/or prevention of caries (enamel/dentineand marginal caries around restorations), as agents for the treatmentand prevention of tooth sensitivity and as carriers for the delivery ofactive substances into teeth. In addition, the peptide structures are ofapplication in the treatment of dentinal/tooth staining, sensitivity andother symptoms experienced in gingival recession. The use of selfassembled peptide structures in caries treatment is demonstrated in thelater examples.

The prior art describes use of an amphiphilic peptide as a scaffold forordered deposition of mineral imitating crystal orientation in bonecollagen [4]. This amphiphilic peptide assembles to give a structurewhich forms fibrils which are stabilised by covalent modification. Theassembly of this peptide differs from the self assembled peptidesdescribed here in that the assembly is driven by amphiphilic forces,rather than by very specific attractions between matched groups in theseparate peptide chains. The amphiphilic peptide described is notsuitable for treatment in vivo as the assembly must take place at low pH(pH<4) and the covalent modification takes place under conditionshostile to living tissues. The self assembled peptide ribbons, fibrilsand fibres described in this application differ in that they can bedesigned such that assembly is triggered at a pH and ionic strengthsuitable for oral application and no subsequent reaction under hostileconditions is necessary.

The prior art also describes use of casein phosphopeptides in dentalapplication [5]. These species are not self assembling peptides asdescribed in this application. As shown in the examples, the selfassembled peptides described in this application show improvedperformance in mineralisation of caries like lesions of enamel undersimulated oral conditions compared with the casein phosphopeptides.

In particular, we provide a method as hereinbefore described wherein themethod comprises the prevention, treatment and/or alleviation of dentalcaries. Thus the method may comprise the mineralisation orremineralisation of a dental cavity or the suppression of leakage aroundexisting restorations. Alternatively, the method may comprisesuppression of demineralisation.

In particular, we provide a method as hereinbefore described wherein themethod comprises the prevention, treatment and/or alleviation of toothsensitivity. Thus the method may comprise the remineralisation of adental cavity, white spot lesions or exposed dentine. Alternatively, themethod may comprise suppression of demineralisation, thus preventingdevelopment of tooth sensitivity.

Although a variety of peptides may be used, one such peptide which maybe mentioned is the P₁₁-8 peptide. A preferred group of peptides whichmay be mentioned are those selected from Table 1A. Table 1B, Table 1Cand Table 1D.

Skin Treatments:

The controlled formation of peptide ribbons, fibrils and/or fibres canbe of benefit in skincare and dermatological applications for bothcosmetic and medical benefit. Benefits may include skin protection,improvement in skin feel, improvement of skin strength, increasedsuppleness, delivery of active or beneficial substances, moisturization,improved appearance and anti-ageing effects.

Hair Care Products:

Peptide ribbons, fibrils and/or fibres can be of benefit in hair care toimprove hair condition, strength, feel, suppleness, appearance andmoisturisation. Peptides which form such structures in application canbe beneficial ingredients in hair shampoos, conditioners, dyes, gels,mousses and other dressings.

In another aspect of the disclosure responsive networks can be used todeliver perfumes, vitamins and/or other beneficial agents to the skinand/or hair. In particular, pH responsiveness can provide control of thedelivery process.

Example 1 Synthesis, Purification and Sterilisation of Peptides

Peptides were synthesized using standard 9-fluorenylmethoxycarbonyl(FMOC) chemistry protocols as described in Aggeli et al. (J. Mat. Chem.,7:1135, 1997). Peptides were purified by reversed-phase HPLC using awater-acetonitrile gradient in the presence of 0.1% trifluoroacetic acidor ammonia as buffer A and 10% buffer A in acetonitrile as buffer B.Mass spectrometry showed the expected molecular weights. Peptides weresterilized in the dry state using γ-irradiation (2.5 MRad) with aGammacell 1000 Elite irradiator. TEM and mass spectrometry were used toassess any damage to the peptide structure and fibril formation.

For, electron microscopy, samples were examined using a Phillips CM10TEM at 80-100 kV accelerating voltage. Gels were diluted to a peptideconcentration of 20 μM seconds before application to a glow-discharged,carbon-coated, copper grid followed by coating with uranyl acetatesolution (4% w/v in water).

Example 2 Peptide P₁₁-8 Forms Solid-Like Gel Network of InterconnectedPositively Charged Fibrils in Cell Culture Medium

The rationally designed peptide P₁₁-8 (Tables 1A and 1C) was dissolvedin 145 mM NaCl, pH˜7.5 aqueous solution (the ionic strength and pHvalues of the solution were similar to those present in cell culturemedium) or it was added directly in cell culture medium. It was foundthat in both solutions, P₁₁-8 self-assembled into twisted beta-sheetfibrils, which had typically narrow width of 4-5 nm, wide width of 12-15nm, full pitch of 200-300 nm, and length of several micrometers.

The main difference between fibrils of P₁₁-3 and of P₁₁-8 is that thoseformed by P₁₁-3 have a net negative charge (−2) per peptide at pH=7.5,whilst those formed by P₁₁-8 have net positive (+2) charge per peptideat pH=7.5.

The fibrils of P₁₁-8 entwined partly with each other forming a threedimensional network and turned the peptide solution in cell media into ahomogeneous self-supporting gel at peptide concentration higher than 15mg/ml. The gel remained stable for at least several weeks at roomtemperature.

The gel could be temporarily broken by mechanical agitation. The time ittook the gel to reform depended on the peptide concentration, rangingfrom seconds for a 35 mg/ml peptide gel, to hours for a 15 mg/ml peptidegel.

Example 3 Contact Cytotoxicity Testing

All of the self-assembling peptide gels assessed for contactcytotoxicity were found to be non-cytotoxic in these experiments. L929murine fibroblasts growing in contact with the negative collagen controlare shown in FIG. 5B and the positive control of cyanoacrylate adhesiveis shown in FIG. 5A. Images showing L929 murine fibroblasts growing incontact with some of the peptides are shown in FIGS. 5C and 5D. Thesewere typical for all the peptides and showed that the peptides testedwere not cytotoxic when placed in culture with L929 fibroblast cells.

Example 4 Amphiphilic Self-Assembling Peptides Carrying a Net NegativeCharge in Physiological Solution

Peptides P₁₁-4, P₁₁-9, P₁₁-15 and P₁₁-17 all carry a net charge of −2 inphysiological conditions. All of these peptides form self-supportinggels at peptide concentrations above 10 mg·ml⁻¹, and for the purposes ofthis study gels were prepared at a concentration of 30 mg·ml⁻¹.

The dimensions of the fibrils formed by these peptides are given inTable 2, and TEM images from which these measurements were obtained areshown in FIGS. 6A-6D. These dimensions are—the length of a peptidefibril (contour length, L), the length of a peptide fibril before itcurves (persistence length, l), the length of a full twist of a peptidefibril (twist pitch, h) the width of a fibril at its widest point(w_(w)) and the width of the fibril at its narrowest point as it twists(w_(n)).

TABLE 2 Fibril dimensions of amphiphilic peptides carrying a netnegative charge in physiological conditions. Peptide L (μm)* l (μm)* h(nm)* w_(n) (nm)* w_(w) (nm)* P₁₁-4 1.2-7 0.7-1.4 132-360 5.5-8 8-14P₁₁-9 1.1-5 0.4-1.3 118-236 3.5-7 7-12 P₁₁-15 1.3-4 0.3-1.2 118-220  5-7 7-10 P₁₁-17   1.3-4.5 0.3-1.7 150-236   5-10 10-16  *L is thefibril contour length, l the fibril persistence length, h the twistpitch, w_(n) the width of the fibril at its narrowest point and w_(w)the width of the fibril at its widest point.

Example 5 Amphiphilic Self-Assembling Peptides Carrying a Net PositiveCharge in Physiological Solution

The peptides P₁₁-8, P₁₁-12, P₁₁-16 and P₁₁-18 all carry a net charge of+2 in physiological conditions and all form self-supporting gels atconcentrations above 10 mg·ml⁻¹. For the purposes of this study peptidegels were prepared at a concentration of 30 mg·ml⁻¹.

A self-supporting gel formed from peptide P₁₁-12 in cell culture mediumis shown in FIG. 7B other TEM images of these peptides are shown inFIGS. 7A, 7C and 7D and the fibril dimensions obtained from measuringthese images are shown in Table 3.

TABLE 3 Fibril dimensions of amphiphilic peptides carrying a netpositive charge in physiological conditions. Peptide L (μm)* l (μm)* h(nm)* w_(n) (nm)* w_(w) (nm)* P₁₁-8 1.2-6.3 0.8-2.5 140-320 4-11 13-19P₁₁-12 1.3-5   0.4-1.2 139-220 5-7  11-16 P₁₁-16 1.2-3.9 0.5-1.6 109-2205-10 11-20 P₁₁-18 1.4-4.2 0.5-1.7 142-236 7-11 11-21 *L is the fibrilcontour length, l the fibril persistence length, h the twist pitch,w_(n) the width of the fibril at its narrowest point and w_(w) the widthof the fibril at its widest point.

Example 6 Polar Self-Assembling Peptides in Physiological Solution

The polar self-assembling peptides are glutamine based and peptideP₁₁-19 carries a net charge of +2 and P₁₁-20 a net charge of −2. The pHresponsive nature of these peptides is the same as that described forthe amphiphilic positively and negatively charged peptides. P₁₁-20 formsa self-assembled gel at concentrations in excess of 20 mg·ml⁻¹, and forthe purpose of this study all gels have been prepared at a concentrationof 30 mg·ml⁻¹. P₁₁-19 does not self assemble at a concentration of 30mg·ml⁻¹, instead forming a viscous fluid. P₁₁-19 does however form aself supporting gel at a peptide concentration of 60 mg·ml⁻¹. TEM imagesof peptides P₁₁-19 and P₁₁-20 are shown in FIGS. 8A and 8B, and thefibril dimensions obtained from measuring TEM images are given in Table4. The fluorine content of peptide P₁₁-20 before and after freeze dryingwas analysed and used to calculate the amount of residual TFA in thepeptide.

TABLE 4 Fibril dimensions of the polar self assembling peptides inphysiological conditions. Peptide L (μm)* l (μm)* h (nm)* w_(n) (nm)*w_(w) (nm)* P₁₁-19 1.5-3   0.5-1   206-356 7-13 15-22 P₁₁-20 0.9-2.80.4-1.5 202-363 8-15 14-20 *L is the fibril contour length, l the fibrilpersistence length, h the twist pitch, w_(n) the width of the fibril atits narrowest point and w_(w) the width of the fibril at its widestpoint.

All of the peptides that self-assemble to form gels at a concentrationof 30 mg·ml⁻¹ have potential for use as scaffolds for cell culture.Altering the polar amino acids present in the peptide does not affectthe ability of the peptides to self-assemble in physiologicalconditions. This re-enforces the hypothesis that it is the net charge of+2 or −2 that drives self-assembly in physiological conditions, and notthe polar amino acid residues present. Examples 4, 5 and 6 have shownthat polar peptides self-assemble forming hydrogels in physiologicalconditions, and not only amphiphilic peptides.

Example 7 Results of the Determination of the Cell Density in PeptideGels by ATPLite Assay

After establishing that the peptides tested were not cytotoxic whenplaced in culture with L929 fibroblast cells, the next stage wasassessing the suitability of the collagen peptide gels for use insupporting cell proliferation.

Peptides P₁₁-9, P₁₁-12 and P₁₁-18 were found to be unsuccessful insupporting cell growth, especially in gels initially seeded with a lowcell concentration. Peptide P₁₁-15 was found to be moderately successfulin supporting cell growth and the gel matrices showed little sign ofmacroscopic degradation. Gels prepared from peptide P₁₁-6 which peptidehad a slightly granular appearance, despite thorough mixing and appearedshrunken at the end of the experiment. Peptide P₁₁-7 appeared to supportcell growth to some degree and peptide P₁₁-20 supported cell growthreasonably well but showed some signs of macroscopic degradation.Collagen gels supplemented with 0.9 mg·ml⁻¹ TFA supported cell growthwith no obvious detrimental effect on the cells and collagen gelssupplemented with 5.1 mg·ml⁻¹ TFA supported cell growth with no visibledetrimental effect on cell growth.

It can be concluded from these studies and the initial gelation studiesthat negatively charged peptides form stronger gels than positivelycharged peptides, as the polar positively charged P₁₁-19 did not gel at30 mg·ml⁻¹ and the amphiphilic positively charged peptides have agreater tendency to dissolve into the supernatant, as shown by the NMRstudies. The positively charged peptides contain two ornithine residueswith side chains ending in an —NH₂ functional group, whereas thenegatively charged peptides contain two glutamic acid residuescontaining a —COOH functional group. —COOH functional groups formstronger hydrogen bonds than —NH₂ groups, leading to the formation ofstronger aggregates. This can explain the different gelation behaviourand dissolution rates seen for the negatively and positively chargedpeptides.

Example 8 De Novo Precipitation of HA Inside Peptide Gels

FIG. 9 shows the normalised phosphate values (positive control=100,negative control=0); peptides normalised against average of positivecontrol (agar gel with polyglutamic acid present) for each run (minusaverage of negative controls for each run); the negative control in eachcase is an agar gel without any protein or peptide added in it.Differing colors/shades in each peptide set represent differing runs. Alevel of 100 indicates that the sample is equal to the positive controlin its ability to precipitate HA de novo. A level of 0% indicates thatthe sample is equal to the negative control in its ability to nucleateand foster the growth of HAP.

Example 9 Effect of Increased or Decreased Charge on Gel Formation

A summary of the experimental data that led to the conclusion that a net−2 or net +2 charge per peptide is required in order to produce stablegel scaffolds in physiological solution conditions. Table 5 shows theSAPs with increasing negative or positive net charges in physiologicalconditions as compared to the original P₁₁-2 peptide (P₁₁-2, SEQ ID NO:13; P₁₁-21, SEQ ID NO: 14; P₁₁-4, SEQ ID NO: 1; P₁₁-22, SEQ ID NO: 15;P₁₁-23, SEQ ID NO: 16; P₁₁-13, SEQ ID NO: 5; P₁₁-3, SEQ ID NO: 17;P₁₁-8, SEQ ID NO: 2; P₁₁-5, SEQ ID NO: 18; P₁₁-14, SEQ ID NO: 6). FIG.10 shows the beta sheet gels are formed at a net peptide charge of +2 or−2 and that a net charge of 0 or +1 or −1 the materials precipitate andabove +2 or below −2 the SAPs are fluid.

TABLE 5 Amphiphilic SAPs with increasing negative orpositive net charge in physiologicalsolution conditions. The charges of primarystructure compared to the original P₁₁-2 molecule are underlined.Net charge Peptide Primary structure at pH = 7.5 P₁₁-2 QQR⁺FQWQFE⁻QQ  0P₁₁-21 QQQFQWQFE⁻QQ -1 P₁₁-4 QQR⁺FE⁻ WE⁻ FE^(±)QQ -2 P₁₁-22 QQQFE⁻ WE⁻FE^(±)QQ -3 P₁₁-23 QQE⁻ FE⁻ WE⁻ FE^(±)QQ -4 P₁₁-13 E⁻ QE⁻ FE⁻ WE⁻FE^(±)QE⁻ -6 P₁₁-3 QQR⁺FQWQFQQQ +1 P₁₁-8 QQR⁺FO⁺ WO⁺ FE^(±)QQ +2 P₁₁-5QQO⁺ FO⁺ WO⁺ FQQQ +3 P₁₁-14 QQO⁺ FO⁺ WO⁺ FO⁺ QQ +4

REFERENCES

-   1. Aggeli, Boden, Semenov, et al., Exploiting protein folding and    misfolding to engineer nanostructured materials, The Biochemist,    22:10-14, 2000.-   2. Nyrkova, Semenov, Aggeli, & Boden, Fibril stability in solutions    of twisted beta-sheet peptides: a new kind of micellisation in    chiral systems, Eur Phys J B, 17, 481-497, 2000.-   3. Nyrkova, Semenov, Aggeli, Bell, Boden, & McLeish, Self-assembly    and structure transformations in living polymers forming fibrils,    Eur Phys J B, 17, 499-513, 2000.-   4. Hartgerink, Beniash, Stupp, Self assembly and mineralisation of    peptide-amphiphile nanofibers SCIENCE 294 (5547): 1684-1688, 2001.-   5. Advances in enamel remineralisation: Casein    phosphopeptide-amorphous calcium Phosphate. Reynolds et al. J. Clin.    Dentistry 10: 86-88, 1999

The invention claimed is:
 1. A self assembling polypeptide (SAP) that forms ribbons, fibrils or fibres in a β-sheet tape-like substructure at physiological pH and physiological salt concentrations, and wherein the polypeptide comprises P₁₁₋₁₇ (TTRFEWEFETT, SEQ ID NO: 9).
 2. A dental product comprising the self-assembling polypeptide of claim
 1. 3. A dental repair or reconstruction or preventative product comprising the self-assembling polypeptide of claim
 1. 4. A tissue engineering scaffold comprising the self-assembling polypeptide of claim
 1. 5. The tissue engineering scaffold according to claim 4, wherein the scaffold is seeded with cells.
 6. A bone repair or reconstruction product comprising the self-assembling polypeptide of claim
 1. 7. The bone repair or reconstruction product according to claim 6, wherein the product is seeded with cells.
 8. A soft tissue or reconstruction product comprising the self-assembling polypeptide of claim
 1. 9. A skin treatment comprising the self-assembling polypeptide of claim
 1. 10. A hair care product comprising the self-assembling polypeptide of claim
 1. 11. A bioresponsive and biocompatible surface comprising the self-assembling polypeptide of claim
 1. 12. The self-assembling polypeptide of claim 1, comprising continuous filaments, yarns, staple, floc, cord, or fabric.
 13. The self-assembling polypeptide of claim 1, further comprising a polymer.
 14. The self-assembling polypeptide of claim 1, wherein the physiological pH is about 7.5.
 15. The self-assembling polypeptide of claim 1, wherein the physiological salt concentration is about 145 mM NaCl.
 16. A composition, comprising: ribbons, fibrils or fibres, wherein each of the ribbons, fibrils or fibres has an antiparallel arrangement of peptides in a β-sheet tape-like substructure at physiological pH and physiological salt concentrations, wherein the composition comprises peptide P₁₁₋₁₇ (TTRFEWEFETT, SEQ ID NO: 9); and a physiological concentration of salt.
 17. The composition of claim 16, wherein the composition comprises fibrils, and wherein the fibrils are comprised in a network of fibrils interconnected at fibre-like junctions.
 18. A dental composition comprising the fibrils of claim
 16. 19. A dental repair or reconstruction or preventative composition comprising the fibrils of claim
 16. 20. The composition of claim 16, wherein the composition is in the form of a tissue engineering scaffold.
 21. The composition according to claim 20, comprising the scaffold seeded with cells.
 22. A bone repair or reconstruction composition comprising the fibrils of claim
 16. 23. A soft tissue or reconstruction composition comprising the fibrils of claim
 16. 24. The composition according to claim 22 that is seeded with cells.
 25. A skin treatment comprising the composition of fibrils of claim
 16. 26. A hair care product comprising the composition of fibrils of claim
 16. 27. A part of a bioresponsive and biocompatible surface comprising the composition of fibrils of claim
 16. 28. The composition of claim 16, wherein the composition comprises continuous filament yarns, staple, floc, cord, or fabric.
 29. The composition of claim 16, further comprising a polymer.
 30. The composition of claim 16, wherein the physiological pH is about 7.5.
 31. The composition of claim 16, wherein the physiological salt concentration is about 145 mM NaCl.
 32. A method of forming a tape, comprising contacting the SAP of claim 1 with an ionic aqueous medium, thereby forming a tape.
 33. A method of forming a gel, comprising contacting the SAP of claim 1 with an ionic aqueous medium, thereby forming a gel.
 34. A method of forming a tape, comprising contacting the composition of claim 16 with an ionic aqueous medium, thereby forming a tape.
 35. A method of forming a gel, comprising contacting the composition of claim 16 with an ionic aqueous medium, thereby forming a gel. 